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WO2015151395A1 - Dispositif de mesure électrochimique - Google Patents

Dispositif de mesure électrochimique Download PDF

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Publication number
WO2015151395A1
WO2015151395A1 PCT/JP2015/000852 JP2015000852W WO2015151395A1 WO 2015151395 A1 WO2015151395 A1 WO 2015151395A1 JP 2015000852 W JP2015000852 W JP 2015000852W WO 2015151395 A1 WO2015151395 A1 WO 2015151395A1
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WO
WIPO (PCT)
Prior art keywords
electrode
electrode exposed
exposed portions
measurement device
electrochemical measurement
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/JP2015/000852
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English (en)
Japanese (ja)
Inventor
篤 守法
正博 安見
高橋　誠
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Panasonic Intellectual Property Management Co Ltd
Original Assignee
Panasonic Intellectual Property Management Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
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Application filed by Panasonic Intellectual Property Management Co Ltd filed Critical Panasonic Intellectual Property Management Co Ltd
Priority to JP2016511347A priority Critical patent/JP6074874B2/ja
Priority to EP15772658.9A priority patent/EP3128000B1/fr
Priority to CN201580016591.4A priority patent/CN106164243B/zh
Publication of WO2015151395A1 publication Critical patent/WO2015151395A1/fr
Priority to US15/277,728 priority patent/US10457907B2/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12M—APPARATUS FOR ENZYMOLOGY OR MICROBIOLOGY; APPARATUS FOR CULTURING MICROORGANISMS FOR PRODUCING BIOMASS, FOR GROWING CELLS OR FOR OBTAINING FERMENTATION OR METABOLIC PRODUCTS, i.e. BIOREACTORS OR FERMENTERS
    • C12M41/00—Means for regulation, monitoring, measurement or control, e.g. flow regulation
    • C12M41/30—Means for regulation, monitoring, measurement or control, e.g. flow regulation of concentration
    • C12M41/34—Means for regulation, monitoring, measurement or control, e.g. flow regulation of concentration of gas
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12M—APPARATUS FOR ENZYMOLOGY OR MICROBIOLOGY; APPARATUS FOR CULTURING MICROORGANISMS FOR PRODUCING BIOMASS, FOR GROWING CELLS OR FOR OBTAINING FERMENTATION OR METABOLIC PRODUCTS, i.e. BIOREACTORS OR FERMENTERS
    • C12M41/00—Means for regulation, monitoring, measurement or control, e.g. flow regulation
    • C12M41/30—Means for regulation, monitoring, measurement or control, e.g. flow regulation of concentration
    • C12M41/36—Means for regulation, monitoring, measurement or control, e.g. flow regulation of concentration of biomass, e.g. colony counters or by turbidity measurements
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/02—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving viable microorganisms
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
    • C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
    • C12Q1/02—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions involving viable microorganisms
    • C12Q1/04—Determining presence or kind of microorganism; Use of selective media for testing antibiotics or bacteriocides; Compositions containing a chemical indicator therefor
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
    • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
    • G01N27/403—Cells and electrode assemblies
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/483—Physical analysis of biological material
    • G01N33/487—Physical analysis of biological material of liquid biological material
    • G01N33/48707—Physical analysis of biological material of liquid biological material by electrical means
    • G01N33/48728—Investigating individual cells, e.g. by patch clamp, voltage clamp
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/5005—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving human or animal cells
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
    • G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
    • G01N33/54366—Apparatus specially adapted for solid-phase testing
    • G01N33/54373—Apparatus specially adapted for solid-phase testing involving physiochemical end-point determination, e.g. wave-guides, FETS, gratings
    • G01N33/5438—Electrodes

Definitions

  • the present disclosure relates to a biological sample electrochemical measurement device used for inspection and analysis of an activity state of a biological sample such as a cell or tissue such as a fertilized egg.
  • Biological samples such as cells and tissues such as fertilized eggs are active by transporting various substances between inside and outside.
  • cardiomyocytes transmit information such as electrical signals and compounds by transporting K ions, Na ions, Ca ions, etc., and control the pulsation of the heart.
  • fertilized eggs take oxygen in the surroundings by breathing, and divide inside the follicle while consuming the taken-in oxygen.
  • a method of holding these biological samples in an electrochemical measurement device and electrically measuring a physicochemical state change generated around the biological sample is known. It has been. These are used as pharmacological tests for new drug candidate compounds using model cells and methods for examining the activity of fertilized eggs.
  • a method for measuring the respiratory activity of a fertilized egg for example, there is a method in which the fertilized egg is captured with a micromanipulator or a micropipette, and the oxygen concentration in the vicinity of the fertilized egg is electrochemically measured using a working electrode. By using this method, the respiratory activity of the fertilized egg can be quantified.
  • the apparatus for measuring the respiratory activity of a fertilized egg is formed by arranging electrodes on a substrate. The entire substrate is covered and insulated with silicon dioxide. Some silicon dioxide is removed and the electrodes are exposed. Three electrodes are arranged. Further, a well for assisting in defining the embryo position is formed on the substrate, and an inverted conical PDMS (Polydimethylsiloxane) well is adhered to the substrate.
  • PDMS Polydimethylsiloxane
  • Patent Document 1 and Patent Document 2 are known.
  • Biological samples such as cells cause physicochemical changes in the surroundings due to activity.
  • changes that occur around the biological sample due to activity may not be uniform and may be biased in a specific direction.
  • fertilized eggs have a polarity in respiratory activity as the developmental stage progresses, so that the amount of oxygen consumed around the fertilized eggs is biased. That is, depending on the direction from the fertilized egg, the respiration rate may change even for the same fertilized egg. Therefore, the conventional respiratory activity measurement device considers the bias of physicochemical changes in the surrounding due to the activity of the biological sample when performing electrochemical measurement of the biological sample, and has a plurality of working electrodes around the biological sample. It is arranged.
  • the respiratory activity measuring device can measure the average activity state of the biological sample by electrochemical measurement by measuring the measured value from each working electrode and calculating the average value or the sum.
  • the conventional respiratory activity measuring device requires the same number of extraction wirings as the working electrode used for the measurement. Therefore, the respiratory activity measuring device has a problem that the number of extraction wirings increases as the number of working electrodes increases.
  • An object of the present invention is to provide an electrochemical measurement device with a small number of extracted wires.
  • an electrochemical measurement device for a biological sample includes a substrate, a sample mounting unit provided on the substrate for mounting the biological sample, and a first sample provided on the substrate and surrounding the sample mounting unit. And a first insulating layer covering the first electrode.
  • the first insulating layer has a plurality of openings, and the first electrode has a plurality of first electrode exposed portions in which a part of the first electrode is exposed from the opening of the first insulating layer.
  • the electrochemical measurement device for a biological sample has a plurality of first electrode exposure portions that are exposed from the insulating layer and are equidistant from the sample placement portion on the electrode provided on the substrate. .
  • the electrochemical measurement device does not require each extraction electrode connected to the plurality of electrode exposed portions, that is, an electrochemical measurement device with a small number of extraction wirings can be realized.
  • FIG. 1 is a top view of a biological sample electrochemical measurement device according to Embodiment 1.
  • FIG. FIG. 2 is a cross-sectional view of the biological sample electrochemical measurement device according to the first embodiment.
  • FIG. 3 is a cross-sectional view showing another example of the biological sample electrochemical measurement device according to the first embodiment.
  • FIG. 4 is a cross-sectional view showing another example of the biological sample electrochemical measurement device according to the first embodiment.
  • FIG. 5 is a top view illustrating another example of the biological sample electrochemical measurement device according to the first embodiment.
  • FIG. 6 is a cross-sectional view schematically showing the operation of the biological sample electrochemical measurement device in the first embodiment.
  • FIG. 7 is a top view of the biological sample electrochemical measurement device according to the second embodiment.
  • FIG. 1 is a top view schematically showing a biological sample electrochemical measurement device 20 in the present embodiment.
  • FIG. 2 is a cross-sectional view taken along line 2-2 of the biological sample electrochemical measurement device 20 shown in FIG.
  • the biological sample electrochemical measurement device 20 includes a substrate 1, a sample placement unit 18 for placing a biological sample provided on the substrate 1, and a first sample surrounding the sample placement unit 18 provided on the substrate 1. It consists of an electrode 3 and a first insulating layer 4 covering the first electrode 3.
  • the first insulating layer 4 has a plurality of openings, and the first electrode 3 is a plurality of first electrodes in which a part of the first electrode 3 is exposed from the plurality of openings of the first insulating layer 4. It has an exposed portion 5.
  • the electrochemical measurement device does not need each extraction electrode connected to the plurality of electrode exposed portions, that is, the number of extraction wirings can be reduced.
  • the substrate 1 is formed of, for example, glass, resin, silicon, or ceramic.
  • the sample mounting portion 18 is, for example, a bottomed hole provided on the upper surface of the substrate 1, that is, a concave portion.
  • the sample placement unit 18 is, for example, a cylindrical or polygonal column hole.
  • the diameter of the sample mounting portion 18 is, for example, 200 ⁇ m.
  • the diameter of the sample mounting part 18 is a value determined according to the size of the biological sample.
  • the depth of the sample mounting part 18 is 80 micrometers, for example. It is preferable that the depth of the sample mounting part 18 is not more than half of the height of the biological sample.
  • the depth of the sample mounting portion 18 By setting the depth of the sample mounting portion 18 to be half or less of the height of the biological sample, the biological sample is exposed from the sample mounting portion 18 and is subjected to physicochemical such as oxygen concentration by the first electrode exposure portion 5. It becomes easy to detect the state change.
  • the depth of the sample mounting portion 18 can be freely set in advance according to the size of the biological sample, and is not limited to half or less of the height of the biological sample.
  • the wall surface 18A of the sample mounting portion 18 and the bottom surface 18B of the sample mounting portion 18 are subjected to a hydrophilic treatment. Since the wall surface 18A and the bottom surface 18B of the sample mounting portion 18 are hydrophilic, the solution can be easily injected into the sample mounting portion 18 and the remaining of bubbles and the like can be suppressed.
  • the hydrophilic treatment of the wall surface 18A and the bottom surface 18B can be performed by, for example, ashing treatment.
  • the sample mounting unit 18 has a wall surface 18A of the sample mounting unit 18 larger than 90 ° with respect to the bottom surface 18B of the sample mounting unit so that the biological sample can be fixed securely. And a tapered shape having an angle smaller than 180 °. As shown in FIG. 4, the sample mounting unit 18 may have a conical or polygonal hole so that the biological sample can be securely fixed.
  • the first electrode 3 is formed on the substrate 1 so as to surround the sample mounting portion 18.
  • the 1st electrode 3 can be made into an elliptical shape, a circular ring shape, or a polygonal shape etc., for example.
  • the first electrode 3 is preferably ring-shaped.
  • the first electrode 3 is preferably concentric with the sample placement portion 18 as the center.
  • the first electrode 3 is made of a noble metal such as platinum, gold, or silver.
  • the 1st electrode 3 may be comprised with the material generally used as an electrode material of a battery, such as carbon and lithium cobaltate.
  • the material of the first electrode 3 may be selected in consideration of the composition of the culture medium at the time of measurement, the necessary voltage, current, and the like.
  • the first electrode 3 has a configuration in which a part of the electrode is interrupted, but may be connected.
  • the first insulating layer 4 is provided on the substrate 1 so as to cover the first electrode 3.
  • the thickness of the first insulating layer 4 is, for example, 0.5 ⁇ m.
  • the first insulating layer 4 is made of silicon dioxide, silicon nitride, organic matter or the like so as to insulate the first electrode 3 from the culture solution.
  • the first insulating layer 4 has an opening on the first electrode 3. Therefore, the first electrode 3 has the first electrode exposed portion 5 in the opening of the first insulating layer 4. The first electrode 3 is in contact with the culture solution at the first electrode exposed portion 5.
  • the opening of the first insulating layer 4 is formed in, for example, a circle or a polygon.
  • the diameter of the first electrode exposed portion 5 is, for example, 5 ⁇ m.
  • the first electrode 3 When the first electrode 3 is not covered with the first insulating layer 4 and the entire first electrode 3 is brought into contact with the culture solution and the electrochemical measurement is performed, an increase in non-Faraday current that becomes noise as the electrode area increases May occur and accurate electrochemical measurement may not be possible.
  • the oxygen consumption accompanying the electrochemical reaction increases as the electrode area increases, affecting the oxygen concentration in the vicinity of the fertilized egg. In some cases, respiratory activity cannot be measured.
  • the area of the first electrode exposed portion 5 is 500 ⁇ m 2 so that the non-Faraday current as measurement noise is reduced and the influence of the oxygen concentration in the vicinity of the fertilized egg due to oxygen consumption accompanying the electrochemical reaction is reduced.
  • the following is preferable.
  • the wiring 6 drawn out from the first electrode 3 is covered with an insulating layer 7.
  • the wiring 6 may not be covered with the insulating layer 7. In this case, the wiring 6 contacts the culture solution.
  • a plurality of first electrode exposed portions 5 are arranged on the first electrode 3 in order to perform measurement at a plurality of positions around the biological sample.
  • the plurality of first electrode exposed portions 5 are preferably arranged at equal intervals.
  • the first electrode exposed portions 5 are arranged at equal intervals every 90 degrees with the sample mounting portion 18 as the center.
  • the first electrode exposed portions 5 may be arranged at equal intervals every 45 degrees with the sample placement portion 18 as the center as shown in FIG. 5. desirable.
  • the plurality of first electrode exposed portions 5 are preferably provided so as to be pointed with respect to the center of the sample mounting portion 18.
  • the first electrode exposed portion 5 forms a diffusion layer in the vicinity of each.
  • the diffusion layer is a region where the concentration distribution of chemical species in the vicinity of the surface of the first electrode exposed portion 5 is not uniform.
  • the chemical species is oxygen. Therefore, the first electrode exposed portion 5 is preferably arranged so that the diffusion layer to be formed does not affect the electrochemical measurement of the other first electrode exposed portion 5.
  • the distance between two adjacent first electrode exposed portions 5 is preferably not less than five times the diameter of the first electrode exposed portion 5.
  • the influence which the diffused layer which the 1st electrode exposed part 5 forms has on the diffused layer which the 1st adjacent electrode exposed part 5 forms can be made small.
  • the current value change due to the respiratory activity of the biological sample can be accurately measured.
  • the distance between two adjacent first electrode exposed portions 5 is 6.5 times or more the diameter of the first electrode exposed portion 5.
  • the diameter of the first electrode exposed portion 5 is the diameter of the smallest circle including the first electrode exposed portion 5 inside.
  • the diameter of the first electrode exposed portion 5 is a diameter.
  • the diameter of the 1st electrode exposure part 5 is the length of a diagonal line.
  • the plurality of first electrode exposed portions 5 are arranged at substantially equidistant positions from the center of the sample placing portion 18.
  • the plurality of first electrode exposed portions 5 are electrically connected by the first electrode 3.
  • the electrochemical measurement device 20 may be provided with a blank electrode 8 on the substrate 1 in order to measure a reference value that is not affected by the activity of the biological sample.
  • the blank electrode 8 is covered with an insulating layer 9 having an opening, and has a blank electrode exposed portion 10 whose surface is exposed from the opening.
  • the insulating layer 9 corresponds to a third insulating layer.
  • the blank electrode 8 is made of the same material as the first electrode 3.
  • One or a plurality of blank electrode exposed portions 10 may be provided. However, the total area of the blank electrode exposed portion 10 is preferably the same as the total area of the first electrode exposed portion 5. More preferably, the number and size of the blank electrode exposed portions 10 are the same as the number and size of the first electrode exposed portions 5. By making the configuration of the blank electrode exposed portion 10 and the first electrode exposed portion 5 the same, it is possible to measure without calculating the reference value.
  • the diameter of the blank electrode exposed portion 10 is, for example, 5 ⁇ m.
  • the blank electrode exposed portion 10 is arranged so that a physicochemical change around the biological sample does not affect an electrochemical reaction generated in the blank electrode exposed portion 10.
  • the distance between the end of the nearest blank electrode exposed portion 10 and the end of the sample mounting portion 18 is preferably 400 ⁇ m or more.
  • the blank electrode exposed portion 10 is overlapped by the diffusion layer formed by the blank electrode exposed portion 10 or the diffusion layer formed by the first electrode exposed portion 5, and the first electrode exposed portion 5 and the blank electrode exposed portion 10 are the same. It is preferably arranged so as not to affect the resulting electrochemical reaction. For example, it is desirable that the closest distance between the end portion of the blank electrode exposed portion 10 and the end portion of the first electrode exposed portion 5 is not less than 5 times the diameter of the first electrode exposed portion 5. More preferably, the closest distance between the end portion of the blank electrode exposed portion 10 and the end portion of the first electrode exposed portion 5 is 6.5 times or more the diameter of the first electrode exposed portion 5.
  • the distance between each of the plurality of blank electrode exposed portions 10 and the first electrode exposed portion 5 may satisfy the above relationship.
  • the nearest distance of the edge part of the blank electrode exposure part 10 and the edge part of the 1st electrode exposure part 5 is set.
  • the sum of the half of the diameter of the first electrode exposed portion 5 and the half of the diameter of the blank electrode exposed portion 10 may be five times or more.
  • the distance between the ends of the adjacent blank electrode exposed portions 10 is preferably 5 times or more the diameter of the blank electrode exposed portion 10. More preferably, the distance between the ends of the adjacent blank electrode exposed portions 10 is at least 6.5 times the diameter of the blank electrode exposed portion 10.
  • the diameter of the blank electrode exposed part 10 is the diameter of the smallest circle including the blank electrode exposed part 10 inside.
  • the diameter of the blank electrode exposed part 10 is a diameter.
  • the diameter of the blank electrode exposure part 10 is the length of a diagonal line.
  • the electrochemical measurement device 20 may be provided with the counter electrode 11 on the substrate 1. Since the counter electrode 11 continuously generates an electrochemical reaction in the first electrode exposed portion 5, the counter electrode 11 generates a reaction opposite to the electrochemical reaction in the first electrode exposed portion 5. That is, the counter electrode 11 is an electrode that is paired with the first electrode that is the working electrode. In the electrochemical measurement device 20, the counter electrode 11 is an electrode that is paired with the first electrode exposed portion 5, which is a working electrode that causes the target target electrochemical reaction. For example, when measuring the dissolved oxygen in the culture solution associated with the respiratory activity of the fertilized egg, the counter electrode 11 supplies an electron necessary for the oxygen reduction reaction in the first electrode exposed portion 5, thus causing an oxidation reaction. .
  • the counter electrode 11 is covered with an insulating layer 12 having an opening.
  • the counter electrode 11 has a counter electrode exposed portion 13 whose surface is exposed from the opening.
  • the insulating layer 12 corresponds to a fourth insulating layer.
  • the counter electrode 11 is formed on the substrate 1 so as to surround the first electrode 3 and the sample mounting portion 18.
  • the counter electrode 11 can have, for example, an elliptical shape, a circular ring shape, or a polygonal shape.
  • the counter electrode 11 is preferably ring-shaped.
  • the counter electrode 11 is preferably concentric with the sample mounting portion 18 as the center.
  • the counter electrode 11 is made of a noble metal such as platinum, gold, or silver.
  • the counter electrode 11 may be made of a material generally used as a battery electrode material such as carbon or lithium cobalt oxide.
  • the material of the counter electrode 11 may be selected in consideration of the composition of the culture solution at the time of measurement, the necessary voltage, current, and the like. Note that the insulating layer 12 is not necessarily provided.
  • the counter electrode exposed portion 13 is preferably arranged so that a physicochemical change around the biological sample does not affect the electrochemical reaction generated in the counter electrode exposed portion 13.
  • the distance between the end of the counter electrode exposed portion 13 and the end of the sample mounting portion 18 is preferably 400 ⁇ m or more.
  • the counter electrode exposed portion 13 has an influence on the electrochemical reaction that occurs in the electrode exposed portions 5, 10, 13 because the diffusion layer formed by the counter electrode exposed portion 13 and the diffusion layer formed by the electrode exposed portions 5, 10 overlap. It is preferable to arrange so as not to affect.
  • the distance between the end portion of the counter electrode exposed portion 13 and the end portions of the electrode exposed portions 5 and 10 is preferably 400 ⁇ m or more.
  • the area of the counter electrode exposed portion 13 is preferably equal to or greater than the total area of the first electrode exposed portion 5.
  • the area of the counter electrode exposed portion 13 is preferably equal to or greater than the total area of the blank electrode exposed portion 10.
  • the counter electrode 11 is not necessarily formed on the substrate 1.
  • the body may be inserted into the culture medium and measured. Further, the counter electrode 11 is not necessarily required and may not be present.
  • the first insulating layer 4, the insulating layer 9 on the blank electrode 8, and the insulating layer 12 on the counter electrode 11 may be composed of the same insulating layer. That is, an insulator may be provided between the first electrode 3, the blank electrode 8, and the counter electrode 11. In this way, by configuring with the same insulating layer, man-hours can be reduced in the manufacturing process.
  • the reference electrode (reference electrode 17 in FIG. 6) is inserted into the culture solution. Platinum or gold is used as the reference electrode material. Further, as another material of the reference electrode, a material containing silver and silver chloride may be used.
  • the diffusion layer formed by the reference electrode and the diffusion layer formed by each of the electrode exposed portions 5, 10, 13 are overlapped so that the electrochemical reaction occurring in the electrode exposed portions 5, 10, 13 is not affected. Preferably they are arranged. For example, the distance between the end portion of the reference electrode and the end portions of the electrode exposed portions 5, 10, and 13 is preferably 400 ⁇ m or more.
  • the reference electrode may be formed on the substrate 1.
  • the first electrode 3 and the blank electrode 8 are individually connected to the measurement amplifier.
  • the potential difference between the first electrode 3 or the blank electrode 8 and the reference electrode and the current due to the electrochemical reaction detected at the first electrode 3 or the blank electrode 8 are individually measured.
  • the substrate 1 is a conductor or a semiconductor, it is preferable to provide an insulating layer (not shown) between the substrate 1 and the first electrode 3.
  • the counter electrode 11 or the reference electrode is provided on the substrate 1, it is preferable to provide an insulating layer between the substrate 1 and the counter electrode 11 or the reference electrode.
  • the insulating layer is made of silicon dioxide, silicon nitride, organic matter, or the like.
  • the outer periphery or peripheral edge of the substrate 1 may be surrounded by a wall.
  • a wall By forming the wall, a well is formed inside the wall.
  • the wall is formed of, for example, glass, resin, silicon, ceramic, silicone rubber, or the like.
  • FIG. 6 is a cross-sectional view schematically showing the operation of the biological sample electrochemical measurement device 20 in the present embodiment.
  • the biological sample is, for example, a cell, a tissue, a fertilized egg, or the like. Concentration gradients are formed radially from active oxygen and metabolites from biological samples.
  • the biological sample 14 is described as a fertilized egg.
  • the electrochemical measuring device 20 is provided with a wall 15 at the periphery. Therefore, a well 16 for introducing a culture solution is formed in a region surrounded by the substrate 1 and the wall 15.
  • a culture solution containing a fertilized egg is injected into the well 16, and the fertilized egg is placed on the sample placement unit 18.
  • the reference electrode 17 is inserted into the culture solution.
  • the reference electrode 17 is provided on the substrate 1, it is not necessary to insert it.
  • the counter electrode 11 is not provided on the substrate 1, the counter electrode is inserted into the culture solution.
  • a potential is applied to the first electrode 3, and a current value due to an electrochemical reaction detected at the first electrode 3 is measured.
  • a reduction reaction of oxygen in the culture solution occurs in the vicinity of the first electrode exposed portion 5.
  • the amount of oxygen reduced in the vicinity of the first electrode exposed portion 5 varies depending on the amount of oxygen in the culture solution.
  • a current corresponding to the oxygen reduction reaction flows through the first electrode 3. Therefore, the amount of dissolved oxygen in the culture solution can be measured by measuring the current value.
  • the amount of dissolved oxygen is related to the amount of oxygen consumed as a result of the activity of a biological sample 14 such as a fertilized egg. Therefore, the activity state of the biological sample 14 such as a fertilized egg can be determined by measuring the dissolved oxygen amount.
  • the counter electrode 11 when measuring the current flowing through the first electrode 3 that is the working electrode, the counter electrode 11 is supplied with electrons necessary for the oxygen reduction reaction of the first electrode exposed portion 5. Apply reverse potential. In this way, by supplying electrons from the counter electrode 11, the electrochemical measurement device 20 can maintain the oxygen reduction reaction in the first electrode exposed portion 5 and perform continuous measurement.
  • the counter electrode 11 is not always necessary and may not be inserted into the culture medium.
  • the blank electrode 8 is used for measuring a reference value of dissolved oxygen in the culture solution that is not affected by the biological sample. A potential similar to that of the first electrode is applied to the blank electrode 8, and the flowing current value is measured. The measurement of the reference value by the blank electrode 8 is performed before or after the measurement by the first electrode 3 or simultaneously. In addition, the structure which does not provide the blank electrode 8 may be sufficient. In this case, the reference value can be measured by applying a potential to the first electrode 3 and measuring the current in the absence of the biological sample.
  • Embodiment 2 an electrochemical measurement device for a biological sample in Embodiment 2 will be described with reference to the drawings.
  • the same components as those in the first embodiment are denoted by the same reference numerals, and detailed description thereof is omitted.
  • FIG. 7 is a top view of the biological sample electrochemical measurement device 30 according to the present embodiment.
  • the difference between the second embodiment and the first embodiment is that the second insulating layer 31 is covered on the substrate 1 of the biological sample electrochemical measurement device 30 so as to surround the first electrode 3.
  • the second electrode 32 is provided. Therefore, the distance between the second electrode exposed portion 33 and the sample mounting portion 18 is larger than the distance between the first electrode exposed portion 5 and the sample mounting portion 18.
  • the biological measurement of the biological sample can be performed at different distances from the sample mounting portion 18. Therefore, the activity state of the biological sample depending on the distance from the biological sample can be monitored.
  • the second electrode 32 can have, for example, an elliptical shape, a circular ring shape, or a polygonal shape.
  • the second electrode 32 is preferably ring-shaped.
  • the second electrode 32 is preferably concentric with the sample mounting portion 18 as the center.
  • the second electrode 32 can be made of the same material as the first electrode 3.
  • the second electrode 32 is made of, for example, a noble metal such as platinum, gold, or silver.
  • the 2nd electrode 32 may be comprised with the material generally used as an electrode material of a battery, such as carbon and lithium cobaltate.
  • the material of the second electrode 32 may be selected in consideration of the composition of the culture medium at the time of measurement, the necessary voltage, current, and the like.
  • the second electrode 32 is covered with a second insulating layer 31.
  • the thickness of the second insulating layer 31 is, for example, 0.5 ⁇ m.
  • the second insulating layer 31 is made of silicon dioxide, silicon nitride, organic matter or the like so as to insulate the second electrode 32 from the culture solution.
  • the second insulating layer 31 has a plurality of openings on the second electrode 32. Therefore, the second electrode 32 has the second electrode exposed portion 33 in the plurality of openings of the second insulating layer 31.
  • the second electrode 32 is in contact with the culture solution at the second electrode exposed portion 33.
  • the opening of the second insulating layer 31 is formed in a circular shape or a polygonal shape.
  • the diameter of the second electrode exposed portion 33 is, for example, 5 ⁇ m.
  • the second electrode 32 When the second electrode 32 is not covered with the second insulating layer 31 and the entire second electrode 32 is brought into contact with the culture solution and electrochemical measurement is performed, an increase in non-Faraday current that becomes noise as the electrode area increases May occur and accurate electrochemical measurement may not be possible.
  • the oxygen consumption accompanying the electrochemical reaction increases as the electrode area increases, affecting the oxygen concentration in the vicinity of the fertilized egg. In some cases, respiratory activity cannot be measured.
  • the area of the second electrode exposed portion 33 is 500 ⁇ m 2 so that the non-Faraday current as measurement noise is reduced and the influence of the oxygen concentration in the vicinity of the fertilized egg due to oxygen consumption accompanying the electrochemical reaction is reduced.
  • the following is preferable.
  • the wiring 34 drawn out from the second electrode 32 is covered with an insulating layer 35.
  • the wiring 34 may not be covered with the insulating layer 35. In this case, the wiring 34 contacts the culture solution.
  • first insulating layer 4 covering the first electrode 3 and the second insulating layer 31 covering the second electrode 32 may be formed of the same insulating layer. By forming with the same insulating layer of one layer, the man-hour of a manufacturing process can be reduced.
  • a plurality of second electrode exposed portions 33 are arranged on the second electrode 32 in order to perform measurement at a plurality of positions around the biological sample.
  • the plurality of second electrode exposed portions 33 are preferably arranged at equal intervals. For example, when four second electrode exposed portions 33 are provided on the second electrode 32, it is desirable that they are arranged at equal intervals every 90 degrees with the sample mounting portion 18 as the center. Further, for example, when eight second electrode exposed portions 33 are provided on the second electrode 32, it is desirable that they are arranged at equal intervals every 45 degrees with the sample mounting portion 18 as the center.
  • the second electrode exposed portion 33 forms a diffusion layer in the vicinity thereof. Therefore, the second electrode exposed portion 33 is preferably arranged so that the diffusion layer to be formed does not affect the electrochemical measurement of the first electrode exposed portion 5 and the other second electrode exposed portion 33. .
  • the distance between the second electrode exposed portion 33 and the adjacent first electrode exposed portion 5 or the second electrode exposed portion 33 is not less than 5 times the diameter of the second electrode exposed portion 33. It is preferable.
  • the adjacent positional relationship means, for example, the closest positional relationship in terms of distance.
  • the influence of the diffusion layer formed by the second electrode exposed portion 33 on the diffusion layer formed by the adjacent first electrode exposed portion 5 or the second electrode exposed portion 33 can be reduced. .
  • the current value change due to the respiratory activity of the biological sample can be accurately measured.
  • the distance between the second electrode exposed portion 33 and the adjacent first electrode exposed portion 5 or the second electrode exposed portion 33 is 6.5 that is the diameter of the second electrode exposed portion 33. It is more than double. With such a configuration, the influence of the diffusion layer formed by the second electrode exposed portion 33 on the diffusion layer formed by the adjacent second electrode exposed portion 33 can be almost eliminated.
  • the second electrode exposed portion 33 of the second electrode 32 is preferably provided between two adjacent first electrode exposed portions 5 of the first electrode 3 when viewed from the sample mounting portion 18. That is, it is preferable that the second electrode exposed portion 33 is provided on a line connecting the midpoint between the two adjacent first electrode exposed portions 5 and the center of the sample mounting portion 18. With this configuration, the first electrode exposed portion 5 and the second electrode exposed portion 33 can be most separated from each other while the distance between the first electrode 3 and the second electrode 32 is reduced.
  • the distance between the second electrode exposed portion 33 of the second electrode 32 and the blank electrode exposed portion 10 is half of the diameter of the second electrode exposed portion 33 and half of the diameter of the blank electrode exposed portion 10. It is preferable that the distance between the counter electrode exposed portion 13 and the reference electrode is 400 ⁇ m or more.
  • the diameter of the second electrode exposed portion 33 is the diameter of the smallest circle including the second electrode exposed portion 33 inside. For example, when the second electrode exposed portion 33 is a circle, the diameter of the second electrode exposed portion 33 is a diameter.
  • the diameter of the 2nd electrode exposure part 33 is the length of a diagonal line.
  • the plurality of second electrode exposed portions 33 are arranged at substantially equidistant positions from the center of the sample mounting portion 18.
  • the plurality of second electrode exposed portions 33 are electrically connected by the second electrode 32.
  • the number and total area of the second electrode exposed portions 33 of the second electrode 32 are preferably the same as the number and total area of the first electrode exposed portions 5 of the first electrode 3.
  • the areas of the first electrode exposed portions 5 are the same size.
  • the areas of the second electrode exposed portions 33 are the same size. Furthermore, one area of the first electrode exposed portion 5 and one area of the second electrode exposed portion 33 have the same size.
  • the second electrode 32 has a configuration in which a part of the electrode is interrupted, but may be connected.
  • the second electrode 32 has a configuration in which a part of the electrode is interrupted.
  • the wiring 6 of the first electrode 3 can be provided in a portion where the second electrode 32 is interrupted.
  • the counter electrode 11 may have a configuration in which a part of the electrode is interrupted.
  • one or more electrodes may be provided outside the second electrode 32.
  • the electrochemical measurement according to the distance from the biological sample can be performed in more detail.
  • the first electrode 3 and the second electrode 32 are each connected to a measurement amplifier, and each current can be measured simultaneously. Thereby, the dissolved oxygen amount etc. which are the physicochemical changes which generate
  • the first electrode 3 and the second electrode 32 may be connected to one measurement amplifier using a switch or a relay, and the time may be divided (time division) for measurement.
  • the apparatus can be reduced in size.
  • a switching circuit it is desirable that the switches and relays operate at high speed. By using a switch or the like that can operate at high speed, it is possible to accurately perform electrochemical measurement around a biological sample with respect to time changes such as the amount of dissolved oxygen.
  • the electrochemical measurement device for a biological sample has a plurality of first electrode exposure portions installed at positions equidistant from the sample placement portion. With this configuration, it is possible to detect the total value of physicochemical state changes, such as oxygen concentration, in multiple directions near the biological sample, and measure the physicochemical state changes around the biological sample on average. can do.
  • the first electrode exposed portion is a part of the first electrode covered with the first insulating layer, the plurality of first electrode exposed portions are electrically connected by the first electrode. It is connected. For this reason, it is possible to acquire information on the total value of changes in physicochemical state such as oxygen concentration of biological samples in a plurality of directions from a single wiring.
  • a plurality of second electrodes are provided outside the first electrode.
  • the concentration gradient of dissolved oxygen amount can be measured from the electric current which flows between the 1st electrode or 2nd electrode from which a distance with a biological sample differs, and a reference electrode.
  • a physicochemical change in which the periphery of the biological sample is spatially resolved can be easily measured.
  • the term indicating the direction such as the upper surface indicates a relative direction that depends only on the relative positional relationship of the components of the electrochemical measurement device, and does not indicate an absolute direction such as a vertical direction. Absent.
  • the electrochemical measurement device has been described based on the embodiment.
  • the present disclosure is not limited to this embodiment. Unless it deviates from the gist of the present disclosure, various modifications conceived by those skilled in the art have been made in this embodiment, and forms constructed by combining components in different embodiments are also within the scope of one or more aspects. May be included.
  • This disclosure can be used for an electrochemical measurement device that electrochemically measures the activity state of a biological sample such as a cell or tissue such as a fertilized egg.

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Abstract

　L'invention concerne un dispositif de mesure électrochimique (20) pourvu d'un substrat (1), d'une partie (18) de montage d'échantillon disposée sur le substrat (1) pour le montage d'un échantillon biologique, d'une première électrode (3) disposée sur le substrat (1) et entourant la partie de montage (18) d'échantillon et d'une première couche isolante (4) pour le recouvrement de la première électrode (3). La première couche isolante (4) a une pluralité d'ouvertures et la première électrode (3) a une pluralité de parties d'exposition d'électrode (5) dans lesquelles des parties de la première électrode (3) sont exposées par les ouvertures dans la première couche isolante (4).
PCT/JP2015/000852 2014-03-31 2015-02-23 Dispositif de mesure électrochimique Ceased WO2015151395A1 (fr)

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JP2016511347A JP6074874B2 (ja) 2014-03-31 2015-02-23 電気化学測定デバイス
EP15772658.9A EP3128000B1 (fr) 2014-03-31 2015-02-23 Dispositif de mesure électrochimique
CN201580016591.4A CN106164243B (zh) 2014-03-31 2015-02-23 电化学测定器件
US15/277,728 US10457907B2 (en) 2014-03-31 2016-09-27 Electrochemical measurement device

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WO2018066358A1 (fr) * 2016-10-06 2018-04-12 日本航空電子工業株式会社 Dispositif de mesure électrochimique et transducteur
JPWO2017068778A1 (ja) * 2015-10-22 2018-08-09 パナソニックＩｐマネジメント株式会社 電気化学測定デバイスおよび電気化学測定システム
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US11940440B2 (en) 2015-11-20 2024-03-26 Japan Aviation Electronics Industry, Limited Electrochemical measurement method, electrochemical measurement device and transducer
EP4212863A1 (fr) * 2015-11-20 2023-07-19 Japan Aviation Electronics Industry, Limited Dispositif de mesure électrochimique et transducteur
US11016078B2 (en) 2015-11-20 2021-05-25 Japan Aviation Electronics Industry, Limited Electrochemical measurement method, electrochemical measurement device and transducer
TWI612138B (zh) * 2015-12-22 2018-01-21 日本航空電子工業股份有限公司 電化學測定方法、電化學測定裝置及傳感器
US10690624B2 (en) 2015-12-22 2020-06-23 Japan Aviation Electronics Industry, Limited Electrochemical measurement method, electrochemical measurement device and transducer
JP6086412B1 (ja) * 2015-12-22 2017-03-01 日本航空電子工業株式会社 電気化学測定方法、電気化学測定装置及びトランスデューサ
WO2017110258A1 (fr) * 2015-12-22 2017-06-29 日本航空電子工業株式会社 Procédé de mesure électrochimique, dispositif de mesure électrochimique et transducteur
US10732137B2 (en) 2016-04-26 2020-08-04 Japan Aviation Electronics Industry, Limited Electrochemical measurement method, electrochemical measurement apparatus and transducer
JP2017198493A (ja) * 2016-04-26 2017-11-02 日本航空電子工業株式会社 電気化学測定方法、電気化学測定装置及びトランスデューサ
WO2017187661A1 (fr) * 2016-04-26 2017-11-02 日本航空電子工業株式会社 Procédé de mesure électrochimique, appareil de mesure électrochimique et transducteur
JP2018059823A (ja) * 2016-10-06 2018-04-12 日本航空電子工業株式会社 電気化学測定装置及びトランスデューサ
WO2018066358A1 (fr) * 2016-10-06 2018-04-12 日本航空電子工業株式会社 Dispositif de mesure électrochimique et transducteur
US11162064B2 (en) 2016-10-06 2021-11-02 Japan Aviation Electronics Industry, Limited Electrochemical measurement device and transducer
US11859167B2 (en) 2016-10-06 2024-01-02 Japan Aviation Electronics Industry, Limited Electrochemical measurement device and transducer

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CN106164243B (zh) 2018-04-27
EP3128000A1 (fr) 2017-02-08
JP2017083462A (ja) 2017-05-18
US10457907B2 (en) 2019-10-29
US20170015971A1 (en) 2017-01-19
JP6501082B2 (ja) 2019-04-17
JP6074874B2 (ja) 2017-02-08
JPWO2015151395A1 (ja) 2017-04-13
EP3128000A4 (fr) 2017-03-29
EP3128000B1 (fr) 2018-05-16

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